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Search Results (527)

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25 pages, 17344 KiB  
Review
Wearable Electrospun Nanofibrous Sensors for Health Monitoring
by Nonsikelelo Sheron Mpofu, Tomasz Blachowicz, Andrea Ehrmann and Guido Ehrmann
Micro 2024, 4(4), 798-822; https://doi.org/10.3390/micro4040049 - 16 Dec 2024
Viewed by 243
Abstract
Various electrospinning techniques can be used to produce nanofiber mats with randomly oriented or aligned nanofibers made of different materials and material mixtures. Such nanofibers have a high specific surface area, making them sensitive as sensors for health monitoring. The entire nanofiber mats [...] Read more.
Various electrospinning techniques can be used to produce nanofiber mats with randomly oriented or aligned nanofibers made of different materials and material mixtures. Such nanofibers have a high specific surface area, making them sensitive as sensors for health monitoring. The entire nanofiber mats are very thin and lightweight and, therefore, can be easily integrated into wearables such as textile fabrics or even patches. Nanofibrous sensors can be used not only to analyze sweat but also to detect physical parameters such as ECG or heartbeat, movements, or environmental parameters such as temperature, humidity, etc., making them an interesting alternative to other wearables for continuous health monitoring. This paper provides an overview of various nanofibrous sensors made of different materials that are used in health monitoring. Both the advantages of electrospun nanofiber mats and their potential problems, such as inhomogeneities between different nanofiber mats or even within one electrospun specimen, are discussed. Full article
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Figure 1

Figure 1
<p>Needle-based electrospinning in a (<b>a</b>) vertical and (<b>b</b>) horizontal setup. Reprinted from [<a href="#B20-micro-04-00049" class="html-bibr">20</a>], with permission from Elsevier.</p>
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<p>Needle-based electrospinning in a (<b>a</b>) vertical and (<b>b</b>) horizontal setup. Reprinted from [<a href="#B20-micro-04-00049" class="html-bibr">20</a>], with permission from Elsevier.</p>
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<p>Diagrams of (<b>a</b>) a roller electrospinning machine; (<b>b</b>) a wire electrospinning machine. From [<a href="#B27-micro-04-00049" class="html-bibr">27</a>], originally published under a CC BY license.</p>
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<p>Schematic electrospinning setup for collecting continuous aligned fibers: (<b>a</b>) fast-rotating cylindrical collector (reprinted from [<a href="#B33-micro-04-00049" class="html-bibr">33</a>], with permission from Elsevier); (<b>b</b>) collector from two conductive silicon (Si) stripes separated by a gap (reprinted (adapted) with permission from [<a href="#B34-micro-04-00049" class="html-bibr">34</a>]). Copyright 2003 American Chemical Society.</p>
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<p>(<b>a</b>) Yarn-spinning setup with water bath-grounded collector electrode; (<b>b</b>) the top view of the yarn formation process. (<b>a</b>,<b>b</b>) Reprinted from [<a href="#B39-micro-04-00049" class="html-bibr">39</a>], with permission from Elsevier.</p>
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<p>(<b>a</b>–<b>c</b>) Scanning electron microscopy (SEM) images of the gelatin fibers produced at 20% (<span class="html-italic">w</span>/<span class="html-italic">v</span>) in formic acid at various conditions. The distance between the tip and the metal collector was 15 cm, and the applied voltage was set to 15 kV. The flow rate varied between 2.5 and 10 μL per min. (<b>d</b>–<b>f</b>) The applied voltage varied from 10 to 20 kV, keeping the distance between the tip and metal plate at a constant value of 15 cm, along with a constant flow rate of 5 μL/min. Reprinted from [<a href="#B49-micro-04-00049" class="html-bibr">49</a>], with permission from Elsevier.</p>
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<p>(<b>a</b>) Free-surface electrospinning from wire electrodes, illustrated for a single liquid. The liquid bath (gold) is charged to a high voltage. As the spindle of wires rotates counterclockwise (as viewed here), the entrained solution first forms a film, as shown on the first (leftmost) wire, which then breaks up into droplets, as shown on the second (middle) wire. As the spindle rotates, the electric field at the wire increases so that each droplet emits a fluid jet, as shown on the third (rightmost) wire. Evaporation of solvent results in the formation of dry fibers. (<b>b</b>) Evolution of the surface profiles of the two immiscible liquids as the wire (viewed end on) travels through the liquid interfaces. Reprinted from [<a href="#B55-micro-04-00049" class="html-bibr">55</a>], with permission from Elsevier.</p>
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<p>Nanofiber yarn-based fabrics manufactured by traditional textile-forming processes: (<b>A</b>) a simple closed chain stitch structure and a relatively complex weft plain stitch tubing structure by knitting technique; (<b>B</b>) three nanofiber yarn-based braided constructs; (<b>C</b>) “Nano” pattern formed on polyester plain woven fabric by embroidering. Reprinted from [<a href="#B98-micro-04-00049" class="html-bibr">98</a>], with permission from Elsevier.</p>
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<p>(<b>a</b>) Schematic of the fabrication process for the stretchable AM temperature sensor array. TFT: thin film transistor; PET: poly(ethylene terephthalate); (<b>b</b>) assembly of prepared layers, liquid metal injection, and formation of electrical contacts with the Ag NW sticker; SWCNT: walled carbon nanotube; Ag NW: silver nanowires; (<b>c</b>) circuit diagram of the stretchable active-matrix temperature sensor array. Reprinted from [<a href="#B114-micro-04-00049" class="html-bibr">114</a>], with permission from Wiley.</p>
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<p>Schematic diagram of the handheld electrospinning device for skin in situ coating with a nanofiber mat. Reprinted from [<a href="#B123-micro-04-00049" class="html-bibr">123</a>], with permission from Elsevier.</p>
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<p>(<b>a</b>) The figure of five auscultation points on the human skeleton. A: aortic; P: pulmonic; E: Erb’s point; T: tricuspid; M: mitral. (<b>b</b>) The image of the experimental setup for heart sound; (<b>c</b>) the image of the heart sound device worn by the subject on (<b>b</b>); the heart sound waveform measured on-site in five auscultation points including (<b>d</b>) aortic point, (<b>e</b>) pulmonic point, (<b>f</b>) Erb’s point, (<b>g</b>) tricuspid point, and (<b>h</b>) mitral valve point; comparison between (<b>i</b>) ECG signal and (<b>j</b>) heart sound signal; (<b>k</b>) captured signal and (<b>l</b>) source signal of aortic insufficiency heart sound recording; (<b>m</b>) captured signal and (<b>n</b>) source signal of atrial septal defect heart sound recording. Reprinted from [<a href="#B130-micro-04-00049" class="html-bibr">130</a>], originally published under a CC BY-NC-ND license.</p>
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<p>Respiration response curves during continuous different motion states and magnified response curves in the black frame regions. Reprinted from [<a href="#B140-micro-04-00049" class="html-bibr">140</a>], originally published under a CC BY license.</p>
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<p>(<b>a</b>) Response of the sensor to various wrist bending angles; (<b>b</b>) response of the sensor to sideways wrist flicking; (<b>c</b>,<b>d</b>) response of the sensor to deep and normal breathing, respectively; (<b>e</b>,<b>f</b>) response of the sensor to walking in a straight line and spot jogging, respectively. Reprinted from [<a href="#B151-micro-04-00049" class="html-bibr">151</a>], originally published under a CC BY license.</p>
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<p>Schematics of (<b>a</b>,<b>b</b>) the fabrication process of microstructured electrodes, (<b>c</b>) the assembled array as a capacitive pressure sensor, and (<b>d</b>) the performance measurement setup of the sensor. PI: polyimide, PDMS: polydimethylsiloxane, DMF: dimethylformamide, PVDF: polyvinylidene difluoride. Reprinted from [<a href="#B161-micro-04-00049" class="html-bibr">161</a>], with permission from Elsevier.</p>
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<p>Temperature sensing behavior and application of a graphite nanosheet/PA66 nanofiber mat: (<b>a</b>) resistance–temperature curve from 30 °C to 130 °C; (<b>b</b>) resistance response vs. temperature under repeated heating/cooling cycles (between 30 °C and 100 °C); (<b>c</b>) sensing behavior of monitoring the hot wind blown out by a commercial blower and (<b>d</b>) touching a cup filled with hot water. Reprinted from [<a href="#B128-micro-04-00049" class="html-bibr">128</a>], with permission from Elsevier.</p>
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<p>(<b>a</b>) Resistance of the MXene, poly(vinyl alcohol) (PVA), and PVA/MXene film sensor exposed to various relative humidities; (<b>b</b>) dynamic resistance changes of PVA/MXene film sensor exposed to various relative humidities; (<b>c</b>) repeatability of PVA/MXene film sensor; (<b>d</b>) time-dependent resistance response and recovery curves of the PVA/MXene sensor between 11 and 97% rH; (<b>e</b>) resistance of sensor with increasing and decreasing humidity; (<b>f</b>) humidity hysteresis curves of the PVA/MXene nanofibers film sensor. Reprinted from [<a href="#B179-micro-04-00049" class="html-bibr">179</a>], originally published under a CC BY license.</p>
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10 pages, 2044 KiB  
Article
Wearable Surface Electromyography System to Predict Freeze of Gait in Parkinson’s Disease Patients
by Anna Moore, Jinxing Li, Christopher H. Contag, Luke J. Currano, Connor O. Pyles, David A. Hinkle and Vivek Shinde Patil
Sensors 2024, 24(23), 7853; https://doi.org/10.3390/s24237853 - 9 Dec 2024
Viewed by 631
Abstract
Freezing of gait (FOG) is a disabling yet poorly understood paroxysmal gait disorder affecting the vast majority of patients with Parkinson’s disease (PD) as they reach advanced stages of the disorder. Falling is one of the most disabling consequences of a FOG episode; [...] Read more.
Freezing of gait (FOG) is a disabling yet poorly understood paroxysmal gait disorder affecting the vast majority of patients with Parkinson’s disease (PD) as they reach advanced stages of the disorder. Falling is one of the most disabling consequences of a FOG episode; it often results in injury and a future fear of falling, leading to diminished social engagement, a reduction in general fitness, loss of independence, and degradation of overall quality of life. Currently, there is no robust or reliable treatment against FOG in PD. In the absence of reliable and effective treatment for Parkinson’s disease, alleviating the consequences of FOG represents an unmet clinical need, with the first step being reliable FOG prediction. Current methods for FOG prediction and prevention cannot provide real-time readouts and are not sensitive enough to detect changes in walking patterns or balance. To fill this gap, we developed an sEMG system consisting of a soft, wearable garment (pair of shorts and two calf sleeves) embedded with screen-printed electrodes and stretchable traces capable of picking up and recording the electromyography activities from lower limb muscles. Here, we report on the testing of these garments in healthy individuals and in patients with PD FOG. The preliminary testing produced an initial time-to-onset commencement that persisted > 3 s across all patients, resulting in a nearly 3-fold drop in sEMG activity. We believe that these initial studies serve as a solid foundation for further development of smart digital textiles with integrated bio and chemical sensors that will provide AI-enabled, medically oriented data. Full article
(This article belongs to the Section Wearables)
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<p>(<b>A</b>) Illustration of the wearable multi-channel EMG to predict freeze of gait in Parkinson’s disease patients. (<b>B</b>) The soft wearable garments are embedded with EMG sensors.</p>
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<p>Training load and fatigue data from the testing of garments in healthy subjects. (<b>A</b>,<b>B</b>) Visual snapshots of the software app are shown for demonstration purposes only. They showcase how the app can be used to represent the user workout numerically and graphically in various muscle groups. (<b>C</b>) Shown are the bursts of EMG activity corresponding to bicep curls with period of pauses at the onset and between two repetitions. (<b>D</b>) Median Frequency (MDF) plot, a frequency-domain feature used to assess muscle fatigue corresponding to the bicep curls in (<b>C</b>).</p>
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<p>Patterns of EMG activity in quadriceps and hamstring muscles (PD patient). The duration of the lowered EMG activity is indicated by the red windows, while the green arrows denote the onset of the FOG episode. The times shown (seconds) highlight the timing between the lowered EMG activity and the onset of the FOG episode.</p>
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<p>(Zoomed in from <a href="#sensors-24-07853-f003" class="html-fig">Figure 3</a>) EMG patterns demonstrate a 3-fold drop (<span class="html-italic">p</span> = 0.001) in EMG activity prior to FOG compared to normal EMG values. This drop in activity commences 3–4.5 s before the onset of a FOG episode. The duration of the lowered EMG activity prior to FOG is indicated by the red window.</p>
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18 pages, 6956 KiB  
Article
Multifunctional Sensor Array for User Interaction Based on Dielectric Elastomers with Sputtered Metal Electrodes
by Sebastian Gratz-Kelly, Mario Cerino, Daniel Philippi, Dirk Göttel, Sophie Nalbach, Jonas Hubertus, Günter Schultes, John Heppe and Paul Motzki
Materials 2024, 17(23), 5993; https://doi.org/10.3390/ma17235993 - 6 Dec 2024
Viewed by 396
Abstract
The integration of textile-based sensing and actuation elements has become increasingly important across various fields, driven by the growing demand for smart textiles in healthcare, sports, and wearable electronics. This paper presents the development of a small, smart dielectric elastomer (DE)-based sensing array [...] Read more.
The integration of textile-based sensing and actuation elements has become increasingly important across various fields, driven by the growing demand for smart textiles in healthcare, sports, and wearable electronics. This paper presents the development of a small, smart dielectric elastomer (DE)-based sensing array designed for user control input in applications such as human–machine interaction, virtual object manipulation, and robotics. DE-based sensors are ideal for textile integration due to their flexibility, lightweight nature, and ability to seamlessly conform to surfaces without compromising comfort. By embedding these sensors into textiles, continuous user interaction can be achieved, providing a more intuitive and unobtrusive user experience. The design of this DE array draws inspiration from a flexible and wearable version of a touchpad, which can be incorporated into clothing or accessories. Integrated advanced machine learning algorithms enhance the sensing system by improving resolution and enabling pattern recognition, reaching a prediction performance of at least 80. Additionally, the array’s electrodes are fabricated using a novel sputtering technique for low resistance as well as high geometric flexibility and size reducibility. A new crimping method is also introduced to ensure a reliable connection between the sensing array and the custom electronics. The advantages of the presented design, data evaluation, and manufacturing process comprise a reduced structure size, the flexible adaptability of the system to the respective application, reliable pattern recognition, reduced sensor and line resistance, the adaptability of mechanical force sensitivity, and the integration of electronics. This research highlights the potential for innovative, highly integrated textile-based sensors in various practical applications. Full article
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Graphical abstract

Graphical abstract
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<p>(<b>a</b>) Functional principle of DES as (<b>b</b>) strain and (<b>c</b>) force sensors.</p>
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<p>Structure and construction of the sensing array with (<b>a</b>) array design and textile integration idea; (<b>b</b>) schematic of electronics; (<b>c</b>) array and electronics layout with mechanical integration into silicone housing; and (<b>d</b>) perspective system integration with additional textile integrated elements.</p>
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<p>(<b>a</b>) DE membrane stretched by use of a custom-made stretching machine. Silicone caps inhibit cracks of the DE membrane and ensure good adhesion during the stretching process; (<b>b</b>) one side of the modified carrier system with a magnetic foil on top of a metal frame equipped with a channel system (200 µm width, 60 µm deep); upper right image of the magnetic foil topography captured by means of Chromatic White Light Sensor (Fa. FRT, MicroProf200, Bergisch-Gladbach, Germany).</p>
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<p>Process steps for manufacturing the thin-film sensor array, starting with attaching the DE membrane on the silicone caps of the stretch machine. Biaxial pre-stretch of the DE membrane to 44.4% and clamping of the DE membrane to the magnetic carrier, followed by coating with 10 nm nickel on both sides. The relaxation process on the stretching machine is supported by isopropanol, while the entire structuring process is realized in three subsequentially structuring steps. Reinforcements of the contact points by hot-melt adhesive fleece, crimping the connectors, and equipment of the female connectors with sockets show the completion of the thin-film-based DE-sensor array preparation. Subsequent encapsulation of the array increases the functionality and improves the integration for different applications.</p>
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<p>Thin-film-based sensor array; (1)–(9) capacitive sensing areas (structured by UV-picosecond laser); (a)–(c) topside contact points for electrical connection of topside electrodes; (d)–(f) backside contact point for electrical connection of the backside electrodes. As an example, (a) is contacting the topside electrode of the capacities (1), (4), and (7); and (d) is contacting the backside electrodes of the capacities (1), (2), and (3). Thus, all capacitances are electrically connected, and their changes can be detected.</p>
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<p>(<b>a</b>) Topside of one contact point of the DE membrane sensor array equipped with thin film, conductive hot-melt fleece material, and the two female crimp connectors; (<b>b</b>) backside of one contact point; the female crimp connector is pierced through the thin-film DE membrane with the conductive hot-melt fleece.</p>
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<p>Structure of the sensing array silicone housing with preload pistons to enable a force measurement; (<b>a</b>) picture of the housing (top and bottom parts and glued assembled array with crimped contacts); (<b>b</b>) schematic and CAD model of the assembled sensing array and a single sensing element.</p>
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<p>Structure and working principle of the sensing electronics including DES array with silicone housing, crimp connections multiplexers capacitance measurement unit, microcontroller, and power supply with battery charging unit.</p>
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<p>Test setup containing (<b>a</b>) test rig structure, linear motor, load cell, and sensing electronics and (<b>b</b>) pictures with the sensing array and piston.</p>
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<p>Single element measurements including force–displacement; force–capacitance; and displacement–capacitance measurements for different piston geometries (diameter and height).</p>
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<p>Capacitance measurement comparison for the whole 3 × 3 array with LCR meter vs. custom electronics measurement. The red lines indicate the mechanical stimulated sensor (middle sensor; array position 2 × 2); the blue lines indicate the not mechanically stimulated sensors. The solid lines are the LCR measurements for all sensors and the dashed lines are the sensor electronics measurements switched with the multiplexers.</p>
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<p>PCA of the training data for the stimulation of every array element (component 1,1 to 3,3 and 0,0 (no element pushed)) with the motor for 1 mm deformation and 2 mm deformation.</p>
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<p>Confusion matrices for the O-pattern, stimulated with the linear motor.</p>
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<p>PCA of the measurement data, exemplary for the Z-pattern with (<b>a</b>) linear motor compared to (<b>b</b>) pushing of the individual elements by user 2.</p>
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<p>Confusion matrices for the Z-pattern measurements of different stimulation variations: (<b>a</b>) linear motor-induced deformation; (<b>b</b>) stimulated by user 1 when the single elements are pushed each after another; (<b>c</b>) stimulated by user 1 when the pattern is introduced in a continuous movement of the finger; (<b>d</b>) stimulated by user 2 where the single elements are pushed each after another; (<b>e</b>) stimulated by user 2 when the pattern is pressed as a continuous movement of the finger.</p>
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14 pages, 1053 KiB  
Article
An Efficient pH Detector for Water Contamination Based on Mach–Zehnder Interferometer Application
by Mario Angel Rico-Mendez, Romeo Selvas, Oxana V. Kharissova, Daniel Toral-Acosta, Norma Patricia Puente-Ramirez, Ricardo Chapa-Garcia and Abraham Antonio Gonzalez-Roque
Sci 2024, 6(4), 80; https://doi.org/10.3390/sci6040080 - 2 Dec 2024
Viewed by 533
Abstract
This paper presents a pH sensor with a Mach–Zehnder Interferometer (MZI) that operates in solutions of 4.0, 7.0, and 10.0. The sensor device consists of two tapered sections with dimensions of 1 mm/1 mm/1 mm for down-taper, waist-length, and up-taper, respectively, with a [...] Read more.
This paper presents a pH sensor with a Mach–Zehnder Interferometer (MZI) that operates in solutions of 4.0, 7.0, and 10.0. The sensor device consists of two tapered sections with dimensions of 1 mm/1 mm/1 mm for down-taper, waist-length, and up-taper, respectively, with a separation of 10 mm. The diameter of the waist is 40 μm. This work includes the experimental evaluation of an MZI fiber optic pH sensor at 1559 nm, where 1559 nm represents a specific wavelength chosen for its optimal sensitivity in evaluating the sensor pH detection performance. It is not the central wavelength of the optical fiber, but one of the minimal values selected to enhance the interaction between the evanescent field and the sample, ensuring the reliable detection of pH variations. These sensor dimensions and the functionalized solution of multi-walled carbon nanotubes (MWCNTs) increase the detection of pH in dyes used in the textile industry. Alizarin is a strong anionic red dye that is part of the anthraquinone dye group. The experimental results demonstrated effective detection of pH levels in water contamination involving dye. This development could resolve the problem with Alizarin. The simple fabrication, low cost, and stability of the optical response make this sensor relevant for pH measurements in water contamination. Full article
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Figure 1
<p>In the geometric structure of the sensor, the regions labelled with A, B, and C are 1 mm of length, corresponding to the DT, UT, and WT, respectively, and region B has a diameter of 40 <math display="inline"><semantics> <mi mathvariant="sans-serif">μ</mi> </semantics></math>m.</p>
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<p>Transmission spectrum of the Mach–Zehnder Interferometer (MZI), observed in the absence of an external surrounding medium.</p>
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<p>Simulated evolution of the input electromagnetic field E is highlighted in the taper regions of the optical fiber.</p>
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<p>Simulated transmission spectrum of an MZI featuring two tapers, each with a transition length of 1 mm, a waist length of 40 <math display="inline"><semantics> <mi mathvariant="sans-serif">μ</mi> </semantics></math>m, and a separation of 10 mm between the tapers.</p>
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<p>Setup for pH optical fiber sensor.</p>
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<p>Stability of the output power of pH 4.0 in a period of 50 min; the axis output power was adjusted (shift) for better data appreciation.</p>
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<p>Comparative of the interference spectrum to dip centered at 1559 nm of transmission of MZFI for each pH sample.</p>
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<p>Output power shifting of the central response from the sensor when submerged in buffer pH values of 4 to 10 in a time of 0–50 min.</p>
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<p>Wavelength shifting of the central response from the sensor as a function of the time in a range of 50 min.</p>
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15 pages, 7377 KiB  
Article
Flat-Knitted Double-Tube Structure Capacitive Pressure Sensors Integrated into Fingertips of Fully Fashioned Glove Intended for Therapeutic Use
by Susanne Fischer, Carola Böhmer, Shamima Nasrin, Carmen Sachse and Chokri Cherif
Sensors 2024, 24(23), 7500; https://doi.org/10.3390/s24237500 - 25 Nov 2024
Viewed by 380
Abstract
A therapeutic glove, which enables medical non-professionals to perform physiotherapeutic gripping and holding movements on patients, would significantly improve the healthcare situation in physiotherapy. The glove aims to detect the orthogonal pressure load and provide feedback to the user. The use of textile [...] Read more.
A therapeutic glove, which enables medical non-professionals to perform physiotherapeutic gripping and holding movements on patients, would significantly improve the healthcare situation in physiotherapy. The glove aims to detect the orthogonal pressure load and provide feedback to the user. The use of textile materials for the glove assures comfort and a good fit for the user. This, in turn, implies a textile realization of the sensor system in order to manufacture both the glove and the sensor system in as few process steps as possible, using only one textile manufacturing technique. The flat knitting technology is an obvious choice here. The aim of the study is to develop a textile capacitive pressure sensor that can be integrated into the fingertips of a glove using flat knitting technology and to evaluate its sensor properties with regard to transmission behavior, hysteresis and drift. It was shown that the proposed method of a flat knitting sensor fabrication is suitable for producing both the sensors and the glove in one single process step. In addition, the implementation of an entire glove with integrated pressure sensors, including the necessary electrical connection of the sensor electrodes via knitted conductive paths in three fingers, was successfully demonstrated. Full article
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<p>Advantages of the proposed sensor-tube structure.</p>
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<p>Knitting process of the samples. (<b>a</b>) Base structure starting at the fingertip; (<b>b</b>) double-tube structure starting with insulating protective rows (white); (<b>c</b>) electrode surfaces (dark grey) with insulating protective rows at the sides (white); (<b>d</b>) insulating protective rows at the end of the electrode surfaces (white), wherein the double-tube structure is now finished; (<b>e</b>) inserting the dielectric layer (displayed in yellow); (<b>f</b>) the pocket is closed by knitting; (<b>g</b>) the remaining finger is completed as a simple tubular structure.</p>
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<p>Integrating the dielectric. (<b>a</b>) Inserting the dielectric layer; (<b>b</b>) dielectric layer is positioned in the knitted sensor pocket; (<b>c</b>) closing the sensor pocket; (<b>d</b>) right side/outside and (<b>e</b>) left side/inside of knitted finger sample with integrated sensor.</p>
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<p>Integrating the dielectric. (<b>a</b>) Inserting the dielectric layer; (<b>b</b>) dielectric layer is positioned in the knitted sensor pocket; (<b>c</b>) closing the sensor pocket; (<b>d</b>) right side/outside and (<b>e</b>) left side/inside of knitted finger sample with integrated sensor.</p>
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<p>Test setup for cyclic pressure loading with synchronized capacitance measurement; (<b>1</b>) digital multimeter, (<b>2</b>) cables, (<b>3</b>) stand as cable holder, (<b>4</b>) clamps, (<b>5</b>) universal testing machine for cyclic pressure loading, (<b>6</b>) acrylic plates, (<b>7</b>) sample to be tested, (<b>8</b>) test sample cut open and fixed under testing machine.</p>
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<p>Testing procedure.</p>
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<p>Transmission behavior, hysteresis and drift. (<b>a</b>) Transmission behavior and hysteresis; (A) loading; (B) unloading; (C) mean transmission curve; (D) hysteresis. (<b>b</b>) Drift; (E) capacitance data; (F) drift curve.</p>
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<p>Development of full glove. (<b>a</b>) Schematic of the sensor positions; (<b>b</b>) front of finger with integrated conductive paths; (<b>c</b>) back of finger with integrated conductive paths; (<b>d</b>) schematic of full glove; (<b>e</b>) knitted glove as fully fashioned article including sensors and conductive paths.</p>
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<p>Measured capacitance and the applied forces in absolute values over time; (<b>a</b>) dielectric of 1 mm thickness; (<b>b</b>) dielectric of 2 mm thickness.</p>
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<p>Transmission behavior of the sensors over all cycles. (<b>a</b>) Dielectric of 1 mm thickness; (<b>b</b>) dielectric of 2 mm thickness.</p>
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<p>Transmission behavior of the sensors and resulting hysteresis; 5 cycles with 10 N. (<b>a</b>) Transmission behavior of dielectric of 1 mm thickness and resulting hysteresis (transmission behavior loading phase displayed in blue, transmission behavior unloading phase displayed in red, mean transmission curve displayed in yellow); (<b>b</b>) transmission behavior of dielectric of 2 mm thickness and resulting hysteresis (transmission behavior loading phase displayed in blue, transmission behavior unloading phase displayed in red, mean transmission curve displayed in yellow); (<b>c</b>) resulting gauge factor and standard deviation of dielectrics of 1 mm and 2 mm.</p>
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<p>Hysteresis and drift. (<b>a</b>) Hysteresis values and standard deviation of the sensors with dielectrics of 1 mm and 2 mm thickness; 5 cycles with 10 N; (<b>b</b>) drift of the sensors with a dielectric of 1 mm and 2 mm thickness; all cycles.</p>
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23 pages, 7201 KiB  
Article
Development of Textile-Based Strain Sensors for Compression Measurements in Sportswear (Sports Bra)
by Aqsa Imran, Shahood uz Zaman, Mozzan Razzaq, Ayesha Ahmad and Xuyuan Tao
Sensors 2024, 24(23), 7495; https://doi.org/10.3390/s24237495 - 24 Nov 2024
Viewed by 580
Abstract
Women sports wearer’s comfort and health are greatly impacted by the breast movements and resultant sports bra compression to prevent excessive movement. However, as sports bras are only made in universal sizes, they do not offer the right kind of support that is [...] Read more.
Women sports wearer’s comfort and health are greatly impacted by the breast movements and resultant sports bra compression to prevent excessive movement. However, as sports bras are only made in universal sizes, they do not offer the right kind of support that is required for a certain activity. To prevent this issue, textile-based strain sensors may be utilized to track compression throughout various activities to create activity-specific designed sports bras. Textile-based strain sensors are prepared in this study using various conductive yarns, including steel, Ag-coated polyamide, and polypropylene/steel-blended threads. Various embroidery designs, including straight, zigzag, and square-wave embroidery patterns, etc., were created on knitted fabric and characterized for strain sensing efficiencies. The experiments concluded that strain sensors prepared from polypropylene/steel thread using a 2-thread square-wave design were best performed in terms of linear conductivity, sensitivity of mechanical impact, and wide working range. This best-performed sample was also tested by integrating it into the sportswear for proposed compression measurements in different body movements. Full article
(This article belongs to the Section Wearables)
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<p>Microscopic images of conductive threads. (<b>a</b>) Ag-coated polyamide, (<b>b</b>) steel, (<b>c</b>) polyester/steel-blended, and (<b>d</b>) polypropylene/steel-blended.</p>
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<p>Evolution of elongation versus electric resistance.</p>
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<p>(<b>a</b>) Top view of a customized tensile tester. (<b>b</b>) Side view of a customized tensile tester. (<b>c</b>) Electrical schematic of the tester.</p>
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<p>Experimental setup for testing.</p>
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<p>Pattern designs: (<b>a</b>) straight, (<b>b</b>) 1-thread zigzag, (<b>c</b>) 2-thread zigzag, (<b>d</b>) 3-thread zigzag, (<b>e</b>) 1-thread square-wave, (<b>f</b>) 2-thread square-wave, and (<b>g</b>) 3-thread square-wave.</p>
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<p>Proto samples of six pattern designs.</p>
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<p>Sample testing of the straight design in (<b>a</b>) the horizontal and (<b>b</b>) vertical directions (sample code: A0).</p>
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<p>(<b>a</b>) Sample testing of the zigzag design in both directions (sample code: D1). (<b>b</b>) Sample testing of the square-wave design in both directions (sample code: A4).</p>
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<p>Graph of resistance against changes in length of the Ag-coated polyamide threads (Samples A1–A6). The red straight line is the fit linear line by linear regression.</p>
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<p>Graph of resistance against changes in length of steel threads. The red straight line is the fit linear line by linear regression.</p>
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<p>Graph of resistance against changes in length of polypropylene/steel−blended thread. The red straight line is the fit linear line by linear regression.</p>
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<p>Functional properties of the selected samples. (<b>a</b>) Gauge factor of the selected strain sensors, and (<b>b</b>) working range and resistance change per mm of the selected sensors.</p>
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<p>Repeatability assessment tests for samples A5 and C5.</p>
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<p>Wash analysis for samples A5 and C5.</p>
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<p>Prototype of the integrated sample used for the women wear analysis.</p>
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<p>Simulation of the running activity in CLO 3D. (<b>a</b>–<b>d</b>) various running postures.</p>
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<p>Resistance changes by changing the bra size of sportswear (<b>a</b>) at 10 km/h., (<b>b</b>) 15 km/h., and (<b>c</b>) 20 km/h. (<b>d</b>) Resistance change for accelerating and deaccelerating.</p>
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<p>Resistance changes by changing the bra size of sportswear after 5 washing cycles.</p>
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<p>Graphical representation of the questionnaire for comfort analysis. (<b>a</b>) Size 32C (<b>b</b>) Size 34C (<b>c</b>) Size 36C (<b>d</b>) Size 38C.</p>
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27 pages, 13812 KiB  
Article
A Quantitative Method to Guide the Integration of Textile Inductive Electrodes in Automotive Applications for Respiratory Monitoring
by James Elber Duverger, Victor Bellemin, Patricia Forcier, Justine Decaens, Ghyslain Gagnon and Alireza Saidi
Sensors 2024, 24(23), 7483; https://doi.org/10.3390/s24237483 - 23 Nov 2024
Viewed by 649
Abstract
Induction-based breathing sensors in automobiles enable unobtrusive respiratory rate monitoring as an indicator of a driver’s alertness and health. This paper introduces a quantitative method based on signal quality to guide the integration of textile inductive electrodes in automotive applications. A case study [...] Read more.
Induction-based breathing sensors in automobiles enable unobtrusive respiratory rate monitoring as an indicator of a driver’s alertness and health. This paper introduces a quantitative method based on signal quality to guide the integration of textile inductive electrodes in automotive applications. A case study with a simplified setup illustrated the ability of the method to successfully provide basic design rules about where and how to integrate the electrodes on seat belts and seat backs to gather good quality respiratory signals in an automobile. The best signals came from the subject’s waist, then from the chest, then from the upper back, and finally from the lower back. Furthermore, folding the electrodes before their integration on a seat back improves the signal quality for both the upper and lower back. This analysis provided guidelines with three design rules to increase the chance of acquiring good quality signals: (1) use a multi-electrode acquisition approach, (2) place the electrodes in locations that maximize breathing-induced body displacement, and (3) use a mechanical amplifying method such as folding the electrodes in locations with little potential for breathing-induced displacement. Full article
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<p>Sensing principle’s equivalent circuit. L<sub>e</sub> and R<sub>e</sub> represent the electrode’s inductance and lossy resistance, respectively. The capacitor C<sub>tank</sub>, in parallel with L<sub>e</sub>, creates an LC tank oscillator. The LDC1612 inductive sensing chip drives the LC tank with a current, i<sub>e</sub>, and measures the frequency of the voltage, V<sub>e</sub>.</p>
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<p>Diagram showing the implementation of the sensing principle. The inductive textile electrode generates an analog respiratory signal that is digitized by the LDC1612 inductive sensing chip, then buffered by the STM32 data processing chip, and finally transferred to the computer. A strain gauge strap around the chest generates a reference analog respiratory signal that is digitized by the Biopac data acquisition system and then transferred to the computer.</p>
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<p>Schematic of the circular electrode design. (<b>a</b>) Front view of the circular electrode. It shows the spiral coil (big circle) and the two connectors (little circles) enclosed in the substrate fabric (dotted rectangle). (<b>b</b>) Side view of the circular electrode. It shows the spiral coil (in gray) enclosed in the substrate fabric (in brown) and the covering fabric (in white). The snap-in connectors (in yellow) link the electrode to the acquisition circuit.</p>
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<p>Schematic of the rectangular electrode design. (<b>a</b>) Front view of the rectangular electrode. It shows the rectangular coil (brown, dashed rectangle) and the connectors (two little circles) enclosed in the substrate fabric (big, rounded rectangle). The substrate fabric is wrapped around the seat belt (in sky blue). (<b>b</b>) Side view of the rectangular electrode. It shows the rectangular coil enclosed in the substrate and covering fabrics (in white). The substrate fabric is wrapped around the seat belt (in sky blue). The snap-in connector (in yellow) links the electrode to the acquisition circuit.</p>
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<p>Electrode prototyping. (<b>a</b>) Tajima TMLX-1201 embroidery machine. (<b>b</b>,<b>c</b>) Close-up of the yarn deposition process.</p>
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<p>Samples of electrodes: (<b>a</b>–<b>c</b>) show the circular designs, (<b>d</b>,<b>e</b>) show the rectangular designs, (<b>f</b>) shows a rectangular design on the yarn side.</p>
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<p>Driving seat and electrode positioning on the seat back. The S105L-BKRD simulator racing seat. A foam covered with loop fabric is used as the seat back. The numbers show approximately where the circular electrodes are attached to the loop fabric during the signal acquisition.</p>
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<p>Integration of the electrodes onto the seat back. (<b>a</b>) Close-up of the circular electrodes attached to the seat back. The covering fabric hides the spiral coils. (<b>b</b>) The covering fabric is lifted to expose the spiral coil and the two connectors. (<b>c</b>) The electrode can be folded and then attached to the seat back.</p>
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<p>Integration of the electrodes on the seat belt. The electrode is wrapped around the belt with a VELCRO<sup>®</sup> hook and loop fastener.</p>
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<p>Schematic illustrating signal acquisition on the seat back. Circular electrodes can be placed at up to 8 different positions to acquire respiratory signals, either sequentially or simultaneously.</p>
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<p>Schematic illustrating signal acquisition on the seat belt. Rectangular or circular electrodes can be placed at up to 4 different positions to acquire respiratory signals, either sequentially or simultaneously.</p>
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<p>Full electrode integration. Textile inductive electrodes on the seat belt (positions #1, #2, #3, and #4) and the Biopac MP160 respiration strap are shown. Inductive electrodes on the seat back are not visible, hidden by the subject’s torso.</p>
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<p>Signal preprocessing. (<b>a</b>) Baseline removal example. (<b>b</b>) Signal filtering example. Amplitudes are in standard score unit. The signal was acquired with the electrode A7320 positioned flat on the seat back at position #4.</p>
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<p>Spectral correlation between the reference and inductive respiratory signals. (<b>a</b>) Good spectrum overlap, with a correlation coefficient of 0.94. (<b>b</b>) Poor spectrum overlap, with a correlation coefficient of 0.12. All amplitudes are in normalized units.</p>
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<p>Ranking of the signals based on quality: illustration of the method. Three signals, with high, average, and poor signal quality rankings, are displayed. (<b>a</b>) The good signal can allow peak detection for breathing rate calculation. (<b>b</b>) The average signal can also provide breathing rate but is challenged by baseline wander, light motion artifacts, and light high-frequency noise. (<b>c</b>) The poor signal does not allow breathing rate detection. It suffers from high-amplitude baseline wander, severe motion artifacts, and serious high-frequency noise.</p>
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<p>Ranking of the signals based on quality. These plots provide a closer look at the signals from <a href="#sensors-24-07483-f015" class="html-fig">Figure 15</a> and confirm the conclusions. (<b>a</b>–<b>c</b>) The presence of high-frequency noise increases with a decreasing signal quality ranking. The ability to allow peak detection for breathing rate calculation decreases with a decreasing signal quality ranking.</p>
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<p>Noise profile from the textile electrodes. The SQIs for all the recordings are sorted in decreasing order and plotted. (<b>a</b>) A SBR below 1 indicates that the baseline wander usually has higher power compared to the signal. Baseline wander is therefore a significant contributor to the noise. (<b>b</b>) On the contrary, a high SHR indicates that the high-frequency noise typically has much lower power than the signal and therefore is not an important noise. (<b>c</b>) According to visual inspection of the whole set of signals, motion artifact starts to become severe at a very low level of MMR, generally below 0.2.</p>
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<p>Comparative analysis of the noise profiles: reference vs. textile. The SQIs for all recordings are sorted in decreasing order and plotted for the Biopac reference and the textile electrodes. The reference always displays a higher ratio, resulting in the following: (<b>a</b>) less baseline wander, (<b>b</b>) less high-frequency noise, and (<b>c</b>) less spikes due to motion artifacts.</p>
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<p>Scatter plot of SRM values for several design configurations on the seat back and the seat belt.</p>
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<p>Scatter plot of the SRM values as a function of the electrodes’ self-inductance.</p>
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<p>Scatter plot of the SRM values for recordings with single- and multi-electrode acquisition.</p>
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<p>Verification of the signal-to-baseline ratio, SBR. Baseline wander is inversely proportional to the SBR, as expected.</p>
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<p>Verification of the signal-to-high-frequency-noise ratio, SHR. The presence of high-frequency noise is inversely proportional to the SHR, as expected.</p>
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<p>Verification of the median-to-mean ratio, MMR. The presence and amplitude of motion artifacts are inversely proportional to the MMR, as expected.</p>
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<p>Verification of the spectral correlation, SPC. The presence of a dominant frequency is inversely proportional to the SPC, as expected.</p>
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10 pages, 1519 KiB  
Article
Proof-of-Concept Quantitative Monitoring of Respiration Using Low-Energy Wearable Piezoelectric Thread
by Kenta Horie, Muhammad Salman Al Farisi, Yoshihiro Hasegawa, Miyoko Matsushima, Tsutomu Kawabe and Mitsuhiro Shikida
Electronics 2024, 13(23), 4577; https://doi.org/10.3390/electronics13234577 - 21 Nov 2024
Viewed by 971
Abstract
Currently, wearable sensors can measure vital sign frequencies, such as respiration rate, but they fall short of providing quantitative data, such as respiratory tidal volume. Meanwhile, the airflow at the mouth carries both the frequency and quantitative respiratory signals. In this study, we [...] Read more.
Currently, wearable sensors can measure vital sign frequencies, such as respiration rate, but they fall short of providing quantitative data, such as respiratory tidal volume. Meanwhile, the airflow at the mouth carries both the frequency and quantitative respiratory signals. In this study, we propose a method to calibrate a wearable piezoelectric thread sensor placed on the chest using mouth airflow for accurate quantitative respiration monitoring. Prior to human trials, we introduced an artificial ventilator as a test subject. To validate the proposed concept, we embedded a miniaturized tube airflow sensor at the ventilator’s outlet, which simulates human respiration, and attached a wearable piezoelectric thread to the piston, which moves periodically to mimic human chest movement. The integrated output readings from the wearable sensor aligned with the airflow rate measurements, demonstrating its ability to accurately monitor not only respiration rate but also quantitative metrics such as respiratory volume. Finally, tidal volume measurement was demonstrated using the wearable piezoelectric thread. Full article
(This article belongs to the Section Flexible Electronics)
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<p>Schematics of the piezoelectric thread sensor utilized in this study.</p>
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<p>Schematics of the piezoelectric thread sensor utilized in this study.</p>
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<p>Schematics of the tube airflow rate sensor utilized in this study.</p>
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<p>Calibration measurement of the fabricated airflow rate sensor: (<b>a</b>) Anemometry response for airflow rate measurement, and (<b>b</b>) calorimetry response to distinguish airflow direction.</p>
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<p>Proof-of-concept experimental setup using an artificial ventilator.</p>
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<p>(<b>a</b>) Proof-of-concept experimental results under a 0.5 Hz ventilator operation condition: Output airflow rate, piezoelectric thread sensor output, and the integration of the piezoelectric thread output. (<b>b</b>) Schematics of ventilator movement conditions during each phase shown in (<b>a</b>).</p>
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<p>Proof-of-concept experimental results under (<b>a</b>) 1.0 and (<b>b</b>) 2.0 Hz ventilator operation conditions: Output airflow rate, piezoelectric thread sensor output, and integration of the piezoelectric thread output.</p>
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<p>Correlation between output airflow and integration of the piezoelectric sensor under (<b>a</b>) negative, (<b>b</b>) positive, and (<b>c</b>) absolute airflow rates with a 1 Hz artificial ventilator operation frequency. The dashed line indicates the mathematical approximation equation.</p>
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<p>Airflow rate from the piezoelectric thread sensor measurement.</p>
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<p>Correlation between the absolute airflow rate and integration of the piezoelectric sensor under different artificial ventilator operation frequencies. Dashed lines indicate mathematical approximations.</p>
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23 pages, 19204 KiB  
Article
Investigations of the Interface Design of Polyetheretherketone Filament Yarn Considering Plasma Torch Treatment
by Toty Onggar, Leopold Alexander Frankenbach and Chokri Cherif
Coatings 2024, 14(11), 1424; https://doi.org/10.3390/coatings14111424 - 8 Nov 2024
Viewed by 595
Abstract
Taking advantage of its high-temperature resistance and elongation properties, conductive-coated polyetheretherketone (PEEK) filament yarn can be used as a textile-based electroconductive functional element, in particular as a strain sensor. This study describes the development of electrical conductivity on an inert PEEK filament surface [...] Read more.
Taking advantage of its high-temperature resistance and elongation properties, conductive-coated polyetheretherketone (PEEK) filament yarn can be used as a textile-based electroconductive functional element, in particular as a strain sensor. This study describes the development of electrical conductivity on an inert PEEK filament surface by the deposition of metallic nickel (Ni) layers via an electroless galvanic plating process. To enhance the adhesion properties of the nickel layer, both PEEK multifilament and monofilament yarn surfaces were metalized by plasma torch pretreatment, followed by nickel plating. Electrical characterizations indicate the potential of nickel-coated PEEK for structural monitoring in textile-reinforced composites. In addition, surface energy measurements before and after plasma torch pretreatment, surface morphology, nickel layer thickness, chemical structure changes, and mechanical properties were analyzed and compared with untreated PEEK. The thickness of the Ni layer was measured and showed an average thickness of 1.25 µm for the multifilament yarn and 3.36 µm for the monofilament yarn. FTIR analysis confirmed the presence of new functional groups on the PEEK surface after plasma torch pretreatment, indicating a successful modification of the surface chemistry. Mechanical testing showed an increase in tensile strength after plasma torch pretreatment but a decrease after nickel plating. In conclusion, this study successfully developed conductive PEEK yarns through plasma torch pretreatment and nickel plating. Full article
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<p>PEEK multifilament yarn (<b>a</b>) and PEEK monofilament yarn (<b>b</b>).</p>
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<p>Schematic representation of the simplified continuous plasma torch pretreatment system for PEEK filament yarns.</p>
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<p>Electroless galvanic nickel plating of PEEK filament yarns.</p>
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<p>Four-wire resistance measurement of nickel-plated PEEK filament yarns.</p>
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<p>Chemical structure of PEEK.</p>
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<p>FTIR spectrum of the untreated, plasma-torch-pretreated, and nickel-plated PEEK multifilament yarns.</p>
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<p>Possible degradation reactions on the surface of PEEK filaments during plasma torch pretreatment.</p>
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<p>FTIR spectrum of the untreated, plasma-torch-pretreated, and nickel-plated PEEK monofilament yarns.</p>
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<p>Determination of filament yarn diameter by light microscopy.</p>
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<p>Light microscopy image of untreated (<b>a</b>) and plasma-torch-pretreated (<b>b</b>) PEEK multifilament yarn (sample V2).</p>
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<p>Light microscopy image of untreated (<b>a</b>) and plasma-torch-pretreated (<b>b</b>) PEEK monofilament yarn (sample V3).</p>
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<p>Scanning electron microscopy (SEM) image (1000× (<b>a</b>) and 5000× (<b>b</b>)) of untreated PEEK multifilament yarn.</p>
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<p>SEM image (5000×) of plasma-torch-pretreated PEEK multifilament yarn; influence of increasing treatment distance (sample V1: 2 cm (<b>a</b>); sample V2: 2.5 cm (<b>b</b>) and sample V3: 3 cm (<b>c</b>)) between the plasma torch tip and PEEK surface on the surface.</p>
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<p>SEM image (5000×) of plasma-torch-pretreated PEEK multifilament yarn; influence of increasing yarn speed (sample V10: 1.5 m/min (<b>a</b>), sample V9: 2 m/min (<b>b</b>) and sample V8: 2.5 m/min (<b>c</b>)) during plasma torch pretreatment on the PEEK surface.</p>
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<p>SEM image (5000×) of plasma-torch-pretreated PEEK multifilament yarn; influence of plasma torch power (sample V2 80% (<b>a</b>) and V12 100% (<b>b</b>)) during plasma torch pretreatment on the PEEK surface.</p>
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<p>SEM image (200× (<b>a</b>) and 5000× (<b>b</b>)) of untreated PEEK monofilament yarn.</p>
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<p>SEM image (200× (<b>a</b>) and 500× (<b>b</b>)) of plasma-torch-pretreated PEEK monofilament yarn (sample V4).</p>
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<p>SEM image (1000× (<b>a</b>) and 20,000× (<b>b</b>)) of nickel-plated PEEK multifilament yarn surface.</p>
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<p>SEM image (200× (<b>a</b>) and 10,000× (<b>b</b>)) of nickel-plated PEEK monofilament yarn.</p>
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<p>SEM image of the cross-section of nickel-plated PEEK multifilament yarn (<b>a</b>) and PEEK monofilament yarn (<b>b</b>).</p>
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<p>Tensile properties of untreated, plasma-torch-pretreated, and nickel-plated PEEK multifilament yarn. Lines of different colours mean that several measurements were carried out on one sample.</p>
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<p>Measured electrical resistivity of nickel-plated PEEK multifilament yarn and monofilament yarn as a function of yarn length.</p>
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19 pages, 4784 KiB  
Article
Manufacture and Analysis of a Textile Sensor Response to Chemical Stimulus Using Printing Techniques and Embroidery for Health Protection
by Ewa Skrzetuska, Paulina Szablewska and Aleksander Patalas
Sustainability 2024, 16(22), 9702; https://doi.org/10.3390/su16229702 - 7 Nov 2024
Viewed by 728
Abstract
The development of the field of textronics covers many directions, but the neediest are safety, medicine, and environmental protection. The solutions developed can combine the needs of many people from different social groups and ages. This leads to sustainable socio-economic, scientific and integrated [...] Read more.
The development of the field of textronics covers many directions, but the neediest are safety, medicine, and environmental protection. The solutions developed can combine the needs of many people from different social groups and ages. This leads to sustainable socio-economic, scientific and integrated approaches to sustainable development. The authors, seeing the growing need to monitor air pollution in order to increase safety, decided to develop textronic chemical sensors based on carbon-based inks and metal thread embroidery, sensitive to harmful gases and vapors based on textiles. This was to limit the production of subsequent sensors made in plastic housings containing difficult-to-recycle materials and replace them with sensors incorporated into everyday materials such as clothing, which will inform us about emerging threats not only in the place where a large plastic sensor is placed, but in every place at home, at work and outside where we will be. The authors assume that the sensors can be incorporated into clothing, e.g. work clothes, and can also be fastened from one piece of clothing to another. This increases their economic aspect and usability on a larger scale. Three materials of different composition were tested: cotton, polyester and viscose. These materials were selected based on their properties, namely the easier determination of their ability to achieve full circularity of the final product.Functional and mechanical tests of resistance to factors occurring during everyday use were carried out for the use of systems in clothing materials and to produce roller blinds and curtains. To examine the durability of the systems, electrical conductivity was checked before and after the tests. The results showed changes in resistance values after individual tests and during contact with harmful gases. Particularly noticeable are the differences between samples with embroidery and samples with inkjet paste applied. It was shown that the selected materials are suitable for the intended application, and selected modifications together with conductive materials show proper functioning in detecting harmful gases. This project demonstrates the possibility of creating chemical sensors based on printing techniques using carbon printing pastes and embroidery with a metal thread with silver on a textile substrate. Possible applications considering health and environmental aspects are presented. Full article
(This article belongs to the Section Sustainable Materials)
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<p>Schematics of screen printing.</p>
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<p>Microscopic photos of the embroidered samples. (<b>a</b>) Cotton knit fabric, (<b>b</b>) polyester knit fabric.</p>
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<p>Microscopic photos of the printed samples in comparison to nonprinted. (<b>a</b>) Cotton knit fabric, (<b>b</b>) polyester knit fabric, (<b>c</b>) viscose knit fabric.</p>
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<p>Changes in surface resistance under the influence of acetone for a cotton sample printed with carbon nanotube paste before application processes.</p>
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<p>Changes in surface resistance under the influence of methanol for a polyester sample printed with carbon nanotube and graphene paste before application processes.</p>
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<p>Changes in surface resistance under the influence of toluene for a cotton sample printed with carbon nanotube and graphene paste before application processes.</p>
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16 pages, 6180 KiB  
Article
Textile Fabric Defect Detection Using Enhanced Deep Convolutional Neural Network with Safe Human–Robot Collaborative Interaction
by Syed Ali Hassan, Michail J. Beliatis, Agnieszka Radziwon, Arianna Menciassi and Calogero Maria Oddo
Electronics 2024, 13(21), 4314; https://doi.org/10.3390/electronics13214314 - 2 Nov 2024
Viewed by 1198
Abstract
The emergence of modern robotic technology and artificial intelligence (AI) enables a transformation in the textile sector. Manual fabric defect inspection is time-consuming, error-prone, and labor-intensive. This offers a great possibility for applying more AI-trained automated processes with safe human–robot interaction (HRI) to [...] Read more.
The emergence of modern robotic technology and artificial intelligence (AI) enables a transformation in the textile sector. Manual fabric defect inspection is time-consuming, error-prone, and labor-intensive. This offers a great possibility for applying more AI-trained automated processes with safe human–robot interaction (HRI) to reduce risks of work accidents and occupational illnesses and enhance the environmental sustainability of the processes. In this experimental study, we developed, implemented, and tested a novel algorithm that detects fabric defects by utilizing enhanced deep convolutional neural networks (DCNNs). The proposed method integrates advanced DCNN architectures to automatically classify and detect 13 different types of fabric defects, such as double-ends, holes, broken ends, etc., ensuring high accuracy and efficiency in the inspection process. The dataset is created through augmentation techniques and a model is fine-tuned on a large dataset of annotated images using transfer learning approaches. The experiment was performed using an anthropomorphic robot that was programmed to move above the fabric. The camera attached to the robot detected defects in the fabric and triggered an alarm. A photoelectric sensor was installed on the conveyor belt and linked to the robot to notify it about an impending fabric. The CNN model architecture was enhanced to increase performance. Experimental findings show that the presented system can detect fabric defects with a 97.49% mean Average Precision (mAP). Full article
(This article belongs to the Special Issue Applications of Computer Vision, 3rd Edition)
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<p>Block diagram of the system.</p>
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<p>Flowchart of robot program.</p>
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<p>The experimental setup of the defect detection system.</p>
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<p>Comparison of Image distribution before and after augmentation for defect classes.</p>
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<p>Confusion matrix of the enhanced trained model.</p>
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<p>F1—confidence Curve of the enhanced model.</p>
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<p>F1—confidence Curve of the default model.</p>
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<p>Results after training with enhanced model.</p>
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<p>Real-time detection experiments conducted using the reported model.</p>
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<p>Network architecture of the CNN model.</p>
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<p>Enhanced network architecture of CNN model.</p>
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11 pages, 498 KiB  
Article
Motion Tape Strain During Trunk Muscle Engagement in Young, Healthy Participants
by Spencer Spiegel, Elijah Wyckoff, Jay Barolo, Audrey Lee, Emilia Farcas, Job Godino, Kevin Patrick, Kenneth J. Loh and Sara P. Gombatto
Sensors 2024, 24(21), 6933; https://doi.org/10.3390/s24216933 - 29 Oct 2024
Viewed by 538
Abstract
Background: Motion Tape (MT) is a low-profile, disposable, self-adhesive wearable sensor that measures skin strain. Preliminary studies have validated MT for measuring lower back movement. However, further analysis is needed to determine if MT can be used to measure lower back muscle engagement. [...] Read more.
Background: Motion Tape (MT) is a low-profile, disposable, self-adhesive wearable sensor that measures skin strain. Preliminary studies have validated MT for measuring lower back movement. However, further analysis is needed to determine if MT can be used to measure lower back muscle engagement. The purpose of this study was to measure differences in MT strain between conditions in which the lower back muscles were relaxed versus maximally activated. Methods: Ten participants without low back pain were tested. A matrix of six MTs was placed on the lower back, and strain data were captured under a series of conditions. The first condition was a baseline trial, in which participants lay prone and the muscles of the lower back were relaxed. The subsequent trials were maximum voluntary isometric contractions (MVICs), in which participants did not move, but resisted the examiner force in extension or rotational directions to maximally engage their lower back muscles. The mean MT strain was calculated for each condition. A repeated measures ANOVA was conducted to analyze the effects of conditions (baseline, extension, right rotation, and left rotation) and MT position (1–6) on the MT strain. Post hoc analyses were conducted for significant effects from the overall analysis. Results: The results of the ANOVA revealed a significant main effect of condition (p < 0.001) and a significant interaction effect of sensor and condition (p = 0.01). There were significant differences in MT strain between the baseline condition and the extension and rotation MVIC conditions, respectively, for sensors 4, 5, and 6 (p = 0.01–0.04). The largest differences in MT strain were observed between baseline and rotation conditions for sensors 4, 5, and 6. Conclusions: MT can capture maximal lower back muscle engagement while the trunk remains in a stationary position. Lower sensors are better able to capture muscle engagement than upper sensors. Furthermore, MT captured muscle engagement during rotation conditions better than during extension. Full article
(This article belongs to the Special Issue Advances in Mobile Sensing for Smart Healthcare)
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<p>Motion Tapes (1–6) and motion capture marker placement schematic (<b>left</b>) and on an actual participant (<b>right</b>) [<a href="#B9-sensors-24-06933" class="html-bibr">9</a>].</p>
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<p>Motion Tape strain data (sensors 1–6) and lumbar kinematic data for a representative participant during a left rotation (LROT) MVIC trial.</p>
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<p>Average (standard deviation) strain (resistance in Ω) across all participants for Motion Tapes (sensors) 1–6 during each condition.</p>
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17 pages, 4461 KiB  
Article
A Novel Wearable Sensor for Measuring Respiration Continuously and in Real Time
by Amjad Ali, Yang Wei, Yomna Elsaboni, Jack Tyson, Harry Akerman, Alexander I. R. Jackson, Rod Lane, Daniel Spencer and Neil M. White
Sensors 2024, 24(20), 6513; https://doi.org/10.3390/s24206513 - 10 Oct 2024
Viewed by 1387
Abstract
In this work, a flexible textile-based capacitive respiratory sensor, based on a capacitive sensor structure, that does not require direct skin contact is designed, optimised, and evaluated using both computational modelling and empirical measurements. In the computational study, the geometry of the sensor [...] Read more.
In this work, a flexible textile-based capacitive respiratory sensor, based on a capacitive sensor structure, that does not require direct skin contact is designed, optimised, and evaluated using both computational modelling and empirical measurements. In the computational study, the geometry of the sensor was examined. This analysis involved observing the capacitance and frequency variations using a cylindrical model that mimicked the human body. Four designs were selected which were then manufactured by screen printing multiple functional layers on top of a polyester/cotton fabric. The printed sensors were characterised to detect the performance against phantoms and impacts from artefacts, normally present whilst wearing the device. A sensor that has an electrode ratio of 1:3:1 (sensor, reflector, and ground) was shown to be the most sensitive design, as it exhibits the highest sensitivity of 6.2% frequency change when exposed to phantoms. To ensure the replicability of the sensors, several batches of identical sensors were developed and tested using the same physical parameters, which resulted in the same percentage frequency change. The sensor was further tested on volunteers, showing that the sensor measures respiration with 98.68% accuracy compared to manual breath counting. Full article
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<p>(<b>a</b>) The layout of the designed sensor. (<b>b</b>) The structure of the four sensor designs and ratio combinations of the sensor, reflector, and ground electrode.</p>
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<p>Diagram of simulation methodology conducted to obtain electric field distribution around each sensor design.</p>
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<p>(<b>a</b>) The computed vertical electric field is (1) below the ground electrode, (2) between the ground and reflector electrode (has a high electric field which reaches up to 75,000 v/m due to a thin dielectric layer), (3) between the sensor and phantom (design 1: vertical electrical field peak is 50 v/m higher than the rest of the design), and (4) within the phantom (the phantom is a glass cylinder of 80 mm diameter set to a dielectric constant of 5 with a glass wall thickness of 2.5 mm and filled with water having dielectric constant of 80). (<b>b</b>) The computed horizontal electric field distribution across the four sensor designs.</p>
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<p>The sensor capacitance was recorded when the phantom was located at z = 1, 5, 10, 15, 20, and 25 mm distances. The electric field distribution of the final sensor designs across the perpendicular plane and the parallel plane. The fringing field effect is present at the corners between the sensor and ground electrodes.</p>
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<p>Simulation capacitance results were obtained with 3 phantoms: muscle, acetone, and water. (<b>a</b>) shows the capacitance of each design between the sensor and ground electrodes, which is referred to as Csg and given a blue colour along with its scale on the left side of each graph. The capacitance between the sensor and the object is referred to as Cso, which is given an orange colour along with its orange scales on the right side of each graph. (<b>b</b>) shows each design’s total capacitance toward the phantom.</p>
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<p>(<b>a</b>) The final printed sensor in four designs. (<b>b</b>) SEM images show the different layers and their corresponding average thickness (showing the thickness of each layer).</p>
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<p>(<b>a</b>) Empirical setup to evaluate the sensor response toward phantoms. (<b>b</b>) The equivalent circuit model of the respiratory rate sensor and interfacing circuit.</p>
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<p>Frequency variation measurements obtained empirically when testing 3 different phantoms.</p>
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<p>(<b>a</b>) Design 2’s identical replicas (Sample 1, 2, and 3) from three different batches of screen printing, and (<b>b</b>) their consistently similar %f-c toward mowing away water phantom.</p>
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<p>(<b>a</b>) Humidity variations ranging from 40% to 80% RH at 24 °C cause an average standard deviation of 0.19 in the design 2 response. (<b>b</b>) Temperature variations ranging from 18 °C to 35 °C at 60% relative humidity (RH) impact the response of design 2, resulting in an average standard deviation of 0.34.</p>
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<p>(<b>a</b>) The results of the flexing durability test conducted empirically on the four designs wrapped on cylinders of multiple diameters. (<b>b</b>) The graph shows the four designs’ responses to increasing pressure. (<b>c</b>) The graph shows the impact of rubbing on sensor response.</p>
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<p>(<b>a</b>) The left image shows the sensor that is attached to the lower part of the chest of the test subject in a sedentary position. The middle image shows how the test subject’s torso was divided into nine positions. (<b>b</b>) The sensor was attached to each position and measured the corresponding breathing rate for one minute. Precise frequency peaks corresponding to the breathing rate can be seen when the sensor is attached at positions 4, 7, 8, and 9. (<b>c</b>) shows the sensor’s response for a random breathing rate of 11 and 22 in one minute. (<b>d</b>) The sensor is attached at position 8, while the test subject is in standing posture and took 11 breaths in one minute.</p>
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13 pages, 2371 KiB  
Article
Deflection and Performance Analysis of Shape Memory Alloy-Driven Fiber–Elastomer Composites with Anisotropic Structure
by Anett Endesfelder, Achyuth Ram Annadata, Aline Iobana Acevedo-Velazquez, Markus Koenigsdorff, Gerald Gerlach, Klaus Röbenack, Chokri Cherif and Martina Zimmermann
Materials 2024, 17(19), 4855; https://doi.org/10.3390/ma17194855 - 2 Oct 2024
Viewed by 892
Abstract
Due to their advantageous characteristics, shape memory alloys (SMAs) are prominent representatives in smart materials. They can be used in application fields such as soft robotics, biomimetics, and medicine. Within this work, a fiber–elastomer composite with integrated SMA wire is developed and investigated. [...] Read more.
Due to their advantageous characteristics, shape memory alloys (SMAs) are prominent representatives in smart materials. They can be used in application fields such as soft robotics, biomimetics, and medicine. Within this work, a fiber–elastomer composite with integrated SMA wire is developed and investigated. Bending and torsion occur when the SMA is activated because of the anisotropic structure of the textile. The metrological challenge in characterizing actuators that perform both bending and torsion lies in the large active deformation of the composite and the associated difficulties in fully imaging and analyzing this with optical measurement methods. In this work, a multi-sensor camera system with up to four pairs of cameras connected in parallel is used. The structure to be characterized is recorded from all sides to evaluate the movement in three-dimensional space. The energy input and the time required for an even deflection of the actuator are investigated experimentally. Here, the activation parameters for the practical energy input required for long life with good deflection, i.e., good efficiency, were analyzed. Different parameters and times are considered to minimize the energy input and, thus, to prevent possible overheating and damage to the wire. Thermography is used to evaluate the heating of the SMA wire at different actuation times over a defined time. Full article
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<p>SMA fiber elastomer actuator: (<b>a</b>) layout and structure; (<b>b</b>) dimensions of the specimen; (<b>c</b>) braided Ni-Ti SMA core–sheath structure with copper wire and PA yarns.</p>
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<p>Electrically connected actuator: (<b>a</b>) front side with tracking point pattern; (<b>b</b>) side view of the actuator in initial and deflected state.</p>
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<p>Top view of the test setup with multi-sensor camera system and IR camera for temperature measurement.</p>
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<p>Electrical signals measured on wire surface, set with the parameters: (<b>a</b>) 1.5 A; (<b>b</b>) 1.75 A; (<b>c</b>) 2 A.</p>
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<p>Displacement in Z direction for different actuation modes, 5 s actuation, 45 s switch-off time, time-shifted for better visibility.</p>
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<p>Measured temperature of wire surface. (<b>a</b>) Overview of the active actuator with highlighted wire measurement detail, shown in (<b>b</b>); (<b>b</b>) SMA wire at two temperatures during activation at the setting of 2 A 10 V; (<b>c</b>) temperature over 15 s at different electrical activation parameters.</p>
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<p>Displacement of the Z coordinate of the evaluated soft actuator configuration of switch-on and switch-off times at two different electrical activation modes and times: (<b>a</b>) 5 s switch-on and 45 s switch-off time, (<b>b</b>) 10 s activation and 90 s switch-off time.</p>
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<p>Calculated resistance at different electrical activation parameters over 15 s.</p>
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<p>Three-dimensional deflection of an actuator, activated with 2 A. (<b>a</b>) Overview of the actuator with characterized details; (<b>b</b>) displacement point A: left down; (<b>c</b>) displacement point B: right down; (<b>d</b>) displacement point C: transition between the textile layers; (<b>e</b>) deflection angle α.</p>
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<p>Three-dimensional deflection of an actuator, activated with 2 A. (<b>a</b>) Overview of the actuator with characterized details; (<b>b</b>) displacement point A: left down; (<b>c</b>) displacement point B: right down; (<b>d</b>) displacement point C: transition between the textile layers; (<b>e</b>) deflection angle α.</p>
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<p>(<b>a</b>) Image of a damaged actuator and (<b>b</b>) deflection curve of reduced actuation and fatigue of an actuator, activation with activation setting of 3A, 10 V.</p>
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10 pages, 1334 KiB  
Article
Validation of a Textile-Based Wearable Measuring Electrocardiogram and Breathing Frequency for Sleep Apnea Monitoring
by Florent Baty, Dragan Cvetkovic, Maximilian Boesch, Frederik Bauer, Neusa R. Adão Martins, René M. Rossi, Otto D. Schoch, Simon Annaheim and Martin H. Brutsche
Sensors 2024, 24(19), 6229; https://doi.org/10.3390/s24196229 - 26 Sep 2024
Viewed by 890
Abstract
Sleep apnea (SA) is a prevalent disorder characterized by recurrent events of nocturnal apnea. Polysomnography (PSG) represents the gold standard for SA diagnosis. This laboratory-based procedure is complex and costly, and less cumbersome wearable devices have been proposed for SA detection and monitoring. [...] Read more.
Sleep apnea (SA) is a prevalent disorder characterized by recurrent events of nocturnal apnea. Polysomnography (PSG) represents the gold standard for SA diagnosis. This laboratory-based procedure is complex and costly, and less cumbersome wearable devices have been proposed for SA detection and monitoring. A novel textile multi-sensor monitoring belt recording electrocardiogram (ECG) and breathing frequency (BF) measured by thorax excursion was developed and tested in a sleep laboratory for validation purposes. The aim of the current study was to evaluate the diagnostic performance of ECG-derived heart rate variability and BF-derived breathing rate variability and their combination for the detection of sleep apnea in a population of patients with a suspicion of SA. Fifty-one patients with a suspicion of SA were recruited in the sleep laboratory of the Cantonal Hospital St. Gallen. Patients were equipped with the monitoring belt and underwent a single overnight laboratory-based PSG. In addition, some patients further tested the monitoring belt at home. The ECG and BF signals from the belt were compared to PSG signals using the Bland-Altman methodology. Heart rate and breathing rate variability analyses were performed. Features derived from these analyses were used to build a support vector machine (SVM) classifier for the prediction of SA severity. Model performance was assessed using receiver operating characteristics (ROC) curves. Patients included 35 males and 16 females with a median age of 49 years (range: 21 to 65) and a median apnea-hypopnea index (AHI) of 33 (IQR: 16 to 58). Belt-derived data provided ECG and BF signals with a low bias and in good agreement with PSG-derived signals. The combined ECG and BF signals improved the classification accuracy for SA (area under the ROC curve: 0.98; sensitivity and specificity greater than 90%) compared to single parameter classification based on either ECG or BF alone. This novel wearable device combining ECG and BF provided accurate signals in good agreement with the gold standard PSG. Due to its unobtrusive nature, it is potentially interesting for multi-night assessments and home-based patient follow-up. Full article
(This article belongs to the Special Issue Sensors for Breathing Monitoring)
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<p>Textile multi-sensor belt for continuous monitoring of cardiac and breathing parameters. The left panel displays the belt mounted on the thorax. The right panel displays the skin-facing site of the multi-sensor belt with embroidered electrodes (1) and pressure-sensitive optical fibers (2).</p>
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<p>Patient workflow and numbers of eligible data for sub-analyses.</p>
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<p>Whole-night ECG signal quality of the monitoring belt. Two illustrative patients are presented, including a good quality data set (<b>left panel</b>) and a poor quality data set (<b>right panel</b>). A locally-weighted polynomial regression smoother was applied and is represented by a red line. The whole-night statistics measured by the whole-night averaged Pearson’s correlation coefficient (<math display="inline"><semantics> <mover accent="true"> <mi>r</mi> <mo>¯</mo> </mover> </semantics></math>) and associated standard deviation are provided at the bottom left corner of both panels.</p>
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<p>Bland-Altman agreement analyses comparing whole-night mean instantaneous heart rates (HR, <b>left panel</b>) and mean instantaneous breathing rates (BR, <b>right panel</b>) measured by the belt and PSG. The mean difference (bias) and 95% limits of agreement are represented by dashed lines. The 95% confidence intervals of the mean difference are represented by dotted lines.</p>
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<p>ROC curves of the prediction accuracy of apnea severity from the monitoring belt (<b>left panel</b>) and the PSG (<b>right panel</b>). The area under the curves (AUC) obtained from ECG (blue circles), BF (red circles), and the combined ECG + BF (purple circles) are provided together with the 95% confidence intervals. Smoothing ROC curves are represented by dashed lines.</p>
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